CA2169549C - A tubular intraluminal graft - Google Patents
A tubular intraluminal graft Download PDFInfo
- Publication number
- CA2169549C CA2169549C CA 2169549 CA2169549A CA2169549C CA 2169549 C CA2169549 C CA 2169549C CA 2169549 CA2169549 CA 2169549 CA 2169549 A CA2169549 A CA 2169549A CA 2169549 C CA2169549 C CA 2169549C
- Authority
- CA
- Canada
- Prior art keywords
- intraluminal graft
- tube
- oriented
- graft according
- film
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Expired - Lifetime
Links
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/82—Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
- A61L31/00—Materials for other surgical articles, e.g. stents, stent-grafts, shunts, surgical drapes, guide wires, materials for adhesion prevention, occluding devices, surgical gloves, tissue fixation devices
- A61L31/08—Materials for coatings
- A61L31/10—Macromolecular materials
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/02—Prostheses implantable into the body
- A61F2/04—Hollow or tubular parts of organs, e.g. bladders, tracheae, bronchi or bile ducts
- A61F2/06—Blood vessels
- A61F2/07—Stent-grafts
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/02—Prostheses implantable into the body
- A61F2/04—Hollow or tubular parts of organs, e.g. bladders, tracheae, bronchi or bile ducts
- A61F2/06—Blood vessels
- A61F2/07—Stent-grafts
- A61F2002/072—Encapsulated stents, e.g. wire or whole stent embedded in lining
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/02—Prostheses implantable into the body
- A61F2/04—Hollow or tubular parts of organs, e.g. bladders, tracheae, bronchi or bile ducts
- A61F2/06—Blood vessels
- A61F2/07—Stent-grafts
- A61F2002/075—Stent-grafts the stent being loosely attached to the graft material, e.g. by stitching
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2240/00—Manufacturing or designing of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
- A61F2240/001—Designing or manufacturing processes
-
- Y—GENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
- Y10—TECHNICAL SUBJECTS COVERED BY FORMER USPC
- Y10T—TECHNICAL SUBJECTS COVERED BY FORMER US CLASSIFICATION
- Y10T428/00—Stock material or miscellaneous articles
- Y10T428/13—Hollow or container type article [e.g., tube, vase, etc.]
- Y10T428/1352—Polymer or resin containing [i.e., natural or synthetic]
-
- Y—GENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
- Y10—TECHNICAL SUBJECTS COVERED BY FORMER USPC
- Y10T—TECHNICAL SUBJECTS COVERED BY FORMER US CLASSIFICATION
- Y10T428/00—Stock material or miscellaneous articles
- Y10T428/13—Hollow or container type article [e.g., tube, vase, etc.]
- Y10T428/1352—Polymer or resin containing [i.e., natural or synthetic]
- Y10T428/1369—Fiber or fibers wound around each other or into a self-sustaining shape [e.g., yarn, braid, fibers shaped around a core, etc.]
-
- Y—GENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
- Y10—TECHNICAL SUBJECTS COVERED BY FORMER USPC
- Y10T—TECHNICAL SUBJECTS COVERED BY FORMER US CLASSIFICATION
- Y10T428/00—Stock material or miscellaneous articles
- Y10T428/13—Hollow or container type article [e.g., tube, vase, etc.]
- Y10T428/1352—Polymer or resin containing [i.e., natural or synthetic]
- Y10T428/1376—Foam or porous material containing
-
- Y—GENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
- Y10—TECHNICAL SUBJECTS COVERED BY FORMER USPC
- Y10T—TECHNICAL SUBJECTS COVERED BY FORMER US CLASSIFICATION
- Y10T428/00—Stock material or miscellaneous articles
- Y10T428/13—Hollow or container type article [e.g., tube, vase, etc.]
- Y10T428/1352—Polymer or resin containing [i.e., natural or synthetic]
- Y10T428/1397—Single layer [continuous layer]
-
- Y—GENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
- Y10—TECHNICAL SUBJECTS COVERED BY FORMER USPC
- Y10T—TECHNICAL SUBJECTS COVERED BY FORMER US CLASSIFICATION
- Y10T428/00—Stock material or miscellaneous articles
- Y10T428/31504—Composite [nonstructural laminate]
- Y10T428/3154—Of fluorinated addition polymer from unsaturated monomers
Landscapes
- Health & Medical Sciences (AREA)
- Engineering & Computer Science (AREA)
- Heart & Thoracic Surgery (AREA)
- Biomedical Technology (AREA)
- Vascular Medicine (AREA)
- Life Sciences & Earth Sciences (AREA)
- Animal Behavior & Ethology (AREA)
- General Health & Medical Sciences (AREA)
- Public Health (AREA)
- Veterinary Medicine (AREA)
- Epidemiology (AREA)
- Surgery (AREA)
- Cardiology (AREA)
- Oral & Maxillofacial Surgery (AREA)
- Transplantation (AREA)
- Prostheses (AREA)
- Laminated Bodies (AREA)
- Materials For Medical Uses (AREA)
Abstract
A tubular intraluminal graft for repair-ing body conduits, made from at least one layer of porous expanded PTFE film that has a microstructure having fibrils oriented in at least two directions which are substantially perpendicular to each other. The tubular intra-luminal graft has a wall thickness of less than about 0.25 mm and may have a longitudinally or hellically oriented seamline. Additional re-inforcing components such as reinforcing ribs or braids may also be provided.
Description
A TUBULAR INTRALUMINAL GRAFT
FIELD OF THE INVENTION
f This invention relates to the field of intraluminal grafts and particularly to thin-wall intraluminal grafts useful as a lining for blood vessels or other body conduits.
BACKGROUND OF THE INVENTION
Conventional vascular grafts have long been used for vascular repair in humans and animals. These devices are typically flexible tubes of woven or knitted polyethylene terephthalate or of porous polytetrafluoroethylene (hereinafter PTFE). Grafts of biological origin are also used, these being typically fixed human umbilical or bovine arteries. These conventional vascular grafts usually require invasive surgical methods that expose at least both ends of the segment of vessel to be repaired. Frequently it is necessary to expose the entire length of the vessel segment. These types of repairs consequently cause mayor trauma to the patient with corresponding lengthy recovery periods and may result in occasional mortality.
Alternative methods have evolved which use intraluminal vascular grafts in the form of diametrically-expandable metallic stent structural supports, tubular grafts or a combination of both. These devices are preferably remotely introduced into a body cavity by the use of a catheter type of delivery system. Alternatively they may be directly implanted by invasive surgery. The intent of these methods is to maintain patency after an occluded vessel has been re-opened using balloon angioplasty, laser angioplasty, atherectomy, roto-ablation, invasive surgery, or a combination of these treatments.
Intraluminal vascular grafts can also be used to repair aneurysmal vessels, particularly aortic arteries, by inserting an intraluminal vascular graft within the aneurysmal vessel so that the WO 95/05131 ~ PCT/LTS94/04807 prosthetic withstands the blood pressure forces responsible for creating the aneurysm.
Intraluminal vascular grafts provide a new blood contacting surface within the lumen of a diseased living vessel. Intraluminal ' grafts are not, however, limited to blood vessels; other applications include urinary tracts, biliary ducts, respiratory tracts and the like.
If the intraluminal graft used is of thin enough wall and adequate flexibility, it may be collapsed and inserted into a body conduit at a smaller diameter location remote from the intended repair site. A catheter type of delivery system is then used to move the intraluminal graft into the repair site and then expand its diameter appropriately to conform to the inner surface of the living vessel.
Various attachment methods including the use of expandable metallic stents may be used to secure the intraluminal graft at the desired location without the necessity of invasive surgery.
Intraluminal vascular grafts were suggested as early as 1912 in an article by Alexis Carrel (Results of the permanent intubation of the thoracic aorta. Surg., Gyn and Ob. 1912;15:245-248). U.S. Patent 3,657,744 to Ersek describes a method of using one or more expandable stents to secure a flexible fabric vascular graft intraluminally, the graft and stent having been introduced distally and delivered to the desired position with a separate delivery system.
Choudhury, U. S. Patent 4,140,126, describes a similar method of repairing aortic aneurysms whereby a polyethylene terephthalate vascular graft is fitted at its ends with metal anchoring pins and .
pleated longitudinally to collapse the graft to a size small.enough to allow for distal introduction.
Rhodes, U.S. Patent 5,122,154 and Lee, U.S. Patent 5,123,917, describe endovascular bypass grafts for intraluminal use which comprise a sleeve having at least two diametrically-expandable stems.
Rhodes teaches that the sleeve material is to be made of conventional vascular graft materials such as GORE-TEX~ Vascular Graft (W. L. Gore & Associates, Inc., Flagstaff AZ) or Impra~ graft (Impra, Inc. Tempe AZ). Both the GORE-TEX Vascular Graft and Impra Graft are extruded ' and longitudinally expanded PTFE tubes. Additionally, the GORE-TEX
Vascular Graft possesses an exterior helical wrapping of porous CA 02169549 1999-06-29 ' ' WO 95/05131 PCTIUS94/04807 expanded PTFE film. The difficulty with the use of either the GORE-TEX Vascular Graft or the Impra Graft as the sleeve c~~nponent is that the relatively thick, bulky wall of these extruded, longitudinally expanded PTFE tubes limits the ability of the tube to be contracted S into a small cross-sectional area for insertion into a blood vessel.
For example, the wall thickness of a 6 rtm inside diameter Thin Walled GORE-TEX Vascular Graft is typically 0.4 mm. The thinness of the wall is limited by the difficulty of producing an extruded, longitudinally expanded tube having a thin wall of relatively uniform thickness.
SUMMARY OF THE INVENTION
The present invention is a tubular intraluminal graft comprised of porous expanded PTFE film having a microstructure of nodes interconnected by fibrils, the fibrils being oriented in at least two directions which are substantially perpendicular to each other. These multiaxially-oriented films having either biaxially or multiaxially-oriented fibrils are made by an expansion process as taught by U.S.
Patents 3,953,566; 4,187,390 and 4,482,516. The films are expanded by stretching them in at least two directions. Multiaxially-oriented films include films having biaxially-oriented fibrils that are oriented primarily in two directions that are substantially perpendicular tn each other. Multiaxially-oriented films also include films having multiaxially-oriented fibrils wherein the fibrils are oriented in all directions within the plane of t:he film.
The term expanded is used herein to refer to porous expanded PTFE. The terms expand, expanding and expandable are used herein to refer to diametrically-adjustable intraluminal stents.
Multiaxially-oriented films having either biaxially or multiaxially-oriented fibrils may be made by expanding the film by stretching it in two directions that are substantially perpendicular to each other, for example longitudinally and transversely. Films having multiaxially-oriented fibrils may also be made by expanding the film by stretching it in more than two directions. Conditions that may affect fibril orientation include not only the directions of 169~~g forces applied during expansion, but also expansion rate, expansion amounts, and the use of either simultaneously or sequentially applied expansion forces.
Because porous expanded PTFE films are typically of greatest strength in the directions parallel to the orientation of the fibrils, , an intraluminal graft constructed from these multiaxially-oriented porous expanded PTFE films will have good strength characteristics in all directions. The inventive intraluminal graft has a wall with a thickness of less than about 0.25 mm and preferably less than 0.10 mm.
The wall of the graft comprises at least one layer of the multiaxially-oriented porous expanded PTFE film.
The inventive intraluminal graft has good hoop strength because of the multiaxially-oriented film from which it is made. The graft is flexible and collapsible, thereby allowing it~to be collapsed to a size much smaller than the full inside diameter. The graft is capable of being implanted into a living body in the collapsed state and can therefore be inserted into a conveniently accessible, smaller diameter portion of a body conduit and then transferred to another, larger diameter portion of the body conduit where it is needed with the use of a catheter type of delivery system. One end of the intraluminal graft is then secured by suitable means such as the use of a metallic expandable stent. The use of the .inventive intraluminal graft thus allows for the effective repair of living blood vessels without the trauma typically associated with conventional invasive vascular surgery.
The inventive intraluminal graft may optionally incorporate separate reinforcing ribs intended to serve as additional strength' members. The ribs may be either longitudinally oriented or .
circumferentially oriented as long as they do not prevent the graft from being diametrically collapsed for insertion into the vascular system. These ribs may be in the form of, for example, stringers of PTFE or fluorinated ethylene propylene (hereinafter FEP) of small diameter such as about 0.025 mm to about 0.5 mm. The use of, for example, longitudinally-oriented ribs can add significantly to the longitudinal strength of the graft without appreciably interfering with the ability of the graft to be collapsed in diameter for ease of insertion into a vascular system and then subsequently increased in diameter at a different location within the vascular system. These ribs may easily be incorporated into the graft during construction of the graft, for example, by temporarily attaching the ribs to the surface of a manufacturing mandrel prior to wrapping the mandrel with a layer of porous expanded PTFE film. The mandrel assembly can then be heated adequately to cause the ribs to adhere to the film, after which the mandrel can be removed. The ribs may be located on the luminal surface of the film, on the exterior surface of the film, or between two layers of the film. A braid may also be used as an additional reinforcing component in place of reinforcing ribs.
BRIEF DESCRIPTION OF THE DRAWINGS
Figure 1 is an enlarged schematic representation of a multiaxially-oriented porous expanded PTFE film having biaxially-oriented fibrils used to construct the intraluminal graft of the present invention.
Figure 2 is an enlarged schematic representation of a multiaxially-oriented porous expanded PTFE film having multiaxially-oriented fibrils used to construct the intraluminal graft of the present invention.
Figure 3 is a scanning electron photomicrograph x500 of a multiaxially-oriented porous expanded PTFE film having biaxially-oriented fibrils used to construct the intraluminal graft of the present invention.
Figure 4 is a scanning electron photomicrograph x2000 of a multiaxially-oriented porous expanded PTFE film having multiaxially-oriented fibrils used to construct the intraluminal graft of the present invention.
Figure 5 is a perspective view of an intraluminal graft of the present invention having a longitudinally oriented seamline.
Figure 6 is a perspective view of an intraluminal graft of the present invention having a radially oriented seamline.
Figures 7A, 7B and 7C are cross sectional views of an intraluminal graft of the present invention made from a single layer of film.
FIELD OF THE INVENTION
f This invention relates to the field of intraluminal grafts and particularly to thin-wall intraluminal grafts useful as a lining for blood vessels or other body conduits.
BACKGROUND OF THE INVENTION
Conventional vascular grafts have long been used for vascular repair in humans and animals. These devices are typically flexible tubes of woven or knitted polyethylene terephthalate or of porous polytetrafluoroethylene (hereinafter PTFE). Grafts of biological origin are also used, these being typically fixed human umbilical or bovine arteries. These conventional vascular grafts usually require invasive surgical methods that expose at least both ends of the segment of vessel to be repaired. Frequently it is necessary to expose the entire length of the vessel segment. These types of repairs consequently cause mayor trauma to the patient with corresponding lengthy recovery periods and may result in occasional mortality.
Alternative methods have evolved which use intraluminal vascular grafts in the form of diametrically-expandable metallic stent structural supports, tubular grafts or a combination of both. These devices are preferably remotely introduced into a body cavity by the use of a catheter type of delivery system. Alternatively they may be directly implanted by invasive surgery. The intent of these methods is to maintain patency after an occluded vessel has been re-opened using balloon angioplasty, laser angioplasty, atherectomy, roto-ablation, invasive surgery, or a combination of these treatments.
Intraluminal vascular grafts can also be used to repair aneurysmal vessels, particularly aortic arteries, by inserting an intraluminal vascular graft within the aneurysmal vessel so that the WO 95/05131 ~ PCT/LTS94/04807 prosthetic withstands the blood pressure forces responsible for creating the aneurysm.
Intraluminal vascular grafts provide a new blood contacting surface within the lumen of a diseased living vessel. Intraluminal ' grafts are not, however, limited to blood vessels; other applications include urinary tracts, biliary ducts, respiratory tracts and the like.
If the intraluminal graft used is of thin enough wall and adequate flexibility, it may be collapsed and inserted into a body conduit at a smaller diameter location remote from the intended repair site. A catheter type of delivery system is then used to move the intraluminal graft into the repair site and then expand its diameter appropriately to conform to the inner surface of the living vessel.
Various attachment methods including the use of expandable metallic stents may be used to secure the intraluminal graft at the desired location without the necessity of invasive surgery.
Intraluminal vascular grafts were suggested as early as 1912 in an article by Alexis Carrel (Results of the permanent intubation of the thoracic aorta. Surg., Gyn and Ob. 1912;15:245-248). U.S. Patent 3,657,744 to Ersek describes a method of using one or more expandable stents to secure a flexible fabric vascular graft intraluminally, the graft and stent having been introduced distally and delivered to the desired position with a separate delivery system.
Choudhury, U. S. Patent 4,140,126, describes a similar method of repairing aortic aneurysms whereby a polyethylene terephthalate vascular graft is fitted at its ends with metal anchoring pins and .
pleated longitudinally to collapse the graft to a size small.enough to allow for distal introduction.
Rhodes, U.S. Patent 5,122,154 and Lee, U.S. Patent 5,123,917, describe endovascular bypass grafts for intraluminal use which comprise a sleeve having at least two diametrically-expandable stems.
Rhodes teaches that the sleeve material is to be made of conventional vascular graft materials such as GORE-TEX~ Vascular Graft (W. L. Gore & Associates, Inc., Flagstaff AZ) or Impra~ graft (Impra, Inc. Tempe AZ). Both the GORE-TEX Vascular Graft and Impra Graft are extruded ' and longitudinally expanded PTFE tubes. Additionally, the GORE-TEX
Vascular Graft possesses an exterior helical wrapping of porous CA 02169549 1999-06-29 ' ' WO 95/05131 PCTIUS94/04807 expanded PTFE film. The difficulty with the use of either the GORE-TEX Vascular Graft or the Impra Graft as the sleeve c~~nponent is that the relatively thick, bulky wall of these extruded, longitudinally expanded PTFE tubes limits the ability of the tube to be contracted S into a small cross-sectional area for insertion into a blood vessel.
For example, the wall thickness of a 6 rtm inside diameter Thin Walled GORE-TEX Vascular Graft is typically 0.4 mm. The thinness of the wall is limited by the difficulty of producing an extruded, longitudinally expanded tube having a thin wall of relatively uniform thickness.
SUMMARY OF THE INVENTION
The present invention is a tubular intraluminal graft comprised of porous expanded PTFE film having a microstructure of nodes interconnected by fibrils, the fibrils being oriented in at least two directions which are substantially perpendicular to each other. These multiaxially-oriented films having either biaxially or multiaxially-oriented fibrils are made by an expansion process as taught by U.S.
Patents 3,953,566; 4,187,390 and 4,482,516. The films are expanded by stretching them in at least two directions. Multiaxially-oriented films include films having biaxially-oriented fibrils that are oriented primarily in two directions that are substantially perpendicular tn each other. Multiaxially-oriented films also include films having multiaxially-oriented fibrils wherein the fibrils are oriented in all directions within the plane of t:he film.
The term expanded is used herein to refer to porous expanded PTFE. The terms expand, expanding and expandable are used herein to refer to diametrically-adjustable intraluminal stents.
Multiaxially-oriented films having either biaxially or multiaxially-oriented fibrils may be made by expanding the film by stretching it in two directions that are substantially perpendicular to each other, for example longitudinally and transversely. Films having multiaxially-oriented fibrils may also be made by expanding the film by stretching it in more than two directions. Conditions that may affect fibril orientation include not only the directions of 169~~g forces applied during expansion, but also expansion rate, expansion amounts, and the use of either simultaneously or sequentially applied expansion forces.
Because porous expanded PTFE films are typically of greatest strength in the directions parallel to the orientation of the fibrils, , an intraluminal graft constructed from these multiaxially-oriented porous expanded PTFE films will have good strength characteristics in all directions. The inventive intraluminal graft has a wall with a thickness of less than about 0.25 mm and preferably less than 0.10 mm.
The wall of the graft comprises at least one layer of the multiaxially-oriented porous expanded PTFE film.
The inventive intraluminal graft has good hoop strength because of the multiaxially-oriented film from which it is made. The graft is flexible and collapsible, thereby allowing it~to be collapsed to a size much smaller than the full inside diameter. The graft is capable of being implanted into a living body in the collapsed state and can therefore be inserted into a conveniently accessible, smaller diameter portion of a body conduit and then transferred to another, larger diameter portion of the body conduit where it is needed with the use of a catheter type of delivery system. One end of the intraluminal graft is then secured by suitable means such as the use of a metallic expandable stent. The use of the .inventive intraluminal graft thus allows for the effective repair of living blood vessels without the trauma typically associated with conventional invasive vascular surgery.
The inventive intraluminal graft may optionally incorporate separate reinforcing ribs intended to serve as additional strength' members. The ribs may be either longitudinally oriented or .
circumferentially oriented as long as they do not prevent the graft from being diametrically collapsed for insertion into the vascular system. These ribs may be in the form of, for example, stringers of PTFE or fluorinated ethylene propylene (hereinafter FEP) of small diameter such as about 0.025 mm to about 0.5 mm. The use of, for example, longitudinally-oriented ribs can add significantly to the longitudinal strength of the graft without appreciably interfering with the ability of the graft to be collapsed in diameter for ease of insertion into a vascular system and then subsequently increased in diameter at a different location within the vascular system. These ribs may easily be incorporated into the graft during construction of the graft, for example, by temporarily attaching the ribs to the surface of a manufacturing mandrel prior to wrapping the mandrel with a layer of porous expanded PTFE film. The mandrel assembly can then be heated adequately to cause the ribs to adhere to the film, after which the mandrel can be removed. The ribs may be located on the luminal surface of the film, on the exterior surface of the film, or between two layers of the film. A braid may also be used as an additional reinforcing component in place of reinforcing ribs.
BRIEF DESCRIPTION OF THE DRAWINGS
Figure 1 is an enlarged schematic representation of a multiaxially-oriented porous expanded PTFE film having biaxially-oriented fibrils used to construct the intraluminal graft of the present invention.
Figure 2 is an enlarged schematic representation of a multiaxially-oriented porous expanded PTFE film having multiaxially-oriented fibrils used to construct the intraluminal graft of the present invention.
Figure 3 is a scanning electron photomicrograph x500 of a multiaxially-oriented porous expanded PTFE film having biaxially-oriented fibrils used to construct the intraluminal graft of the present invention.
Figure 4 is a scanning electron photomicrograph x2000 of a multiaxially-oriented porous expanded PTFE film having multiaxially-oriented fibrils used to construct the intraluminal graft of the present invention.
Figure 5 is a perspective view of an intraluminal graft of the present invention having a longitudinally oriented seamline.
Figure 6 is a perspective view of an intraluminal graft of the present invention having a radially oriented seamline.
Figures 7A, 7B and 7C are cross sectional views of an intraluminal graft of the present invention made from a single layer of film.
Figure 8 is a cross sectional view of an intraluminal graft of the present invention made from two layers of film.
Figures 9A, 9B and 9C describe cross sectional views of the intraluminal graft incorporating reinforcing ribs.
Figure 10 describes a perspective view of the intraluminal graft incorporating a reinforcing braid.
DETAILED DESCRIPTION OF THE INYENTION
Figure 1 shows an enlarged schematic representation of the surface microstructure of a multiaxially-oriented film ~0 having biaxially-oriented fibrils wherein nodes ,~1_ are connected by fibrils 13 and fibrils ~5. Fibrils ~3_ and ~5 are oriented respectively in two directions which are substantially perpendicular to each other within the plane of the film. These multiaxially-oriented films having biaxially-oriented fibrils may also contain some fibrils such as fibril 17 that are not parallel to either fibrils ~ or fibrils ~5.
Figure 2 describes an enlarged schematic representation of the surface microstructure of a multiaxially-oriented film ~0 wherein nodes ~ 1 are connected by fi bri l s ,~,~. The f i bri l s ~, are multiaxially-oriented fibrils which are oriented in substantially all directions within the plane of the film wherein virtually all fibrils are oriented substantially perpendicular to some other fibrils.
Figure 3 shows a scanning electron photomicrograph of a multiaxially-oriented porous expanded PTFE film having biaxially-oriented fibrils used to construct examples 1 and 2 described below.
Figure 4 shows a scanning electron photomicrograph of a multiaxially-oriented porous expanded PTFE film having multiaxially-oriented fibrils used to construct example 3 described below.
The tubular intraluminal graft is manufactured by wrapping a multiaxially-oriented porous expanded PTFE film around a mandrel and , forming a seamline by overlapping adjacent edges of the film. As shown by Figure 5, the seamline 51 may be longitudinally-oriented so that it is substantially parallel to the longitudinal axis 53 of the graft 50. After the seamline 51 is formed, the film-wrapped mandrel is placed into an oven set above the melt-point of the PTFE film 55 for a time adequate to cause the overlapping edges of the film to adhere to each other. After heating, the film-wrapped mandrel is removed from the oven and allowed to cool. The mandrel is then removed from within the resulting tubular intraluminal graft.
Alternatively, an adhesive such as FEP may be used between the.
adjacent edges forming the seamline, requiring that the film-wrapped mandrel be heated only adequately to melt the adhesive enough to bond the adjacent edges.
In still another alternative, the PTFE film may be provided with a coating of the adhesive on only one surface of the film.
These adhesive-coated films are oriented during wrapping of the mandrel so that the adhesive-coated side of the film faces away from the surface of the mandrel and therefore contacts only adjacent layers of film and does not contact the mandrel. The adhesive is preferably in the form of a discontinuous coating in order to have a minimal effect on the porosity of the completed thin wall intraluminal graft. The adhesive must be biocompatible; preferred adhesives are thermoplastics of lower melt point than the crystalline melt point of the PTFE film.
Thermoplastic fluoropolymers such as FEP are most preferred.
These types of adhesives are activated by placing the film-wrapped mandrel into an oven at a combination of time and temperature adequate to cause melting of the adhesive.
The FEP-coated porous expanded PTFE film is made by a process which comprises the steps of: .
a) contacting a porous PTFE film with another layer which is preferably a film of FEP or alternatively of another .thermoplastic polymer;
b) heating the composition obtained in step a) to a temperature above the melting point of the thermoplastic polymer;
c) stretching the heated composition of step b) while maintaining the temperature above the melting point of the thermoplastic polymer; and d) cooling the product of step c).
The adhesive coating on the multiaxially-oriented porous expanded PTFE film may be either continuous (non-porous) or discontinuous (porous) depending primarily on the amount and rate of stretching, the WO 95/05131 PC'1'/US94104807 ~1~9~~~
temperature during stretching and the thickness of the adhesive prior to stretching.
As described by Figure 6, the intraluminal graft ~0 may be formed by wrapping a tape ~~, formed by cutting a multiaxially-oriented porous expanded PTFE film into a narrow strip, helically-wrapping the tape 6~ around a mandrel and overlapping adjacent edges of the tape to create a helically-oriented seamline ~. The overlapping adjacent edges may be adhered as described previously for the longitudinally-oriented seamlines 51.
Figure 7A shows a cross section of the intraluminal graft 5Q
having a simple overlapped seamline ~. In an alternative embodiment described by the cross sectional view of Figure 7B, the seamline ~
may be formed as a flange ~ which may optionally be folded over as shown by the cross sectional view of Figure 7C. The seamlines of Figures 7B and 7C are most practical for longitudinally-oriented seamlines; the simple overlapped edge seamline of Figure 7A is preferred for helically-oriented seamlines.
As shown by the cross sectional view of Figure 8, the intraluminal graft may also be made from two or more layers of multiaxially-oriented porous expanded PTFE film by allowing the film to completely overlap itself at least one time. Two or more layer embodiments may be formed by either helically or longitudinally wrapping the film around the mandrel.
lfarious samples of the intraluminal graft of the present invention were constructed and are described below as examples. The methods used to characterize the fibril lengths of the films used to make the grafts, the wall thicknesses of the films and the resulting grafts, and the method used to mechanically test the integrity of the resulting grafts are as follows.
The fibril lengths of the porous expanded PTFE films referred to herein were estimated mean values obtained by examining scanning electron photomicrographs of these films. For multiaxially-oriented films, these estimates included consideration of fibrils oriented in all directions. The mean fibril lengths of the films used to construct the intraluminal grafts of the present invention are ' preferred to be within range of about 5 to about 120 microns, although fibril lengths beyond this range may also be useful.
_g_ Wall thickness measurements of the finished intraluminal grafts were made by longitudinally slitting the wall of a short length of the tubular graft to create a flat sheet. These wall thickness measurements did not include the overlapped edges of the seamlines.
Seamlines are not included in wail thickness measurements unless the width of the seamline is such that the graft is made from two or more layers of film as described by the cross sectional view of Figure 8.
The wall thickness of the flat sheet was measured using a Mitutoyo model no. 2804-10 snap gauge having a part no. 7300 frame, by placing the sheet between the pads of the gauge and gently easing the pads into contact with the sample until the pads were in full contact with the sheet under the full force of the spring-driven snap gauge pads.
Film density values were based on the bulk volume of a film sample using the snap-gauge thickness measurement.
Pressure testing of all samples was accomplished by inserting a length of 6 mm outside diameter tubular latex bladder of about 0.4 mm wall thickness into the lumen of the tubular sample to be tested, clamping off one end of the tubular sample and latex bladder assembly with forceps, and applying air pressure for a period of time as described for each example to the tubular sample and bladder assembly.
Approximately three seconds was required to achieve the described air pressure level; this three second period was not included in the test period. After the release of pressure, the bladder was removed from the tubular sample and the sample was visually inspected for any resulting damage.
A multiaxially-oriented porous expanded PTFE film having biaxially-oriented fibrils as described by Figures 1 and 3 was used to make an intraluminal graft. The film used was of about 30 micron fibril length, about 10 cm width and about .08 mm thickness. A 12 cm long sample of this film was wrapped around a 6 mm diameter stainless steel mandrel forming a longitudinally-oriented seamline as shown by Figures 7B and 7C. The biaxially-oriented fibrils of the film were oriented to be parallel to the circumference of the mandrel and parallel to the longitudinal axis of the mandrel. The film edges were ~:~~~4~
-lo-adhered by using a hot iron shielded with a thin sheet of polyimide film. The iron, having a surface temperature of about 400°C, was applied by hand against the thin sheet of polyimide film and the length of the seamline. The excess material was then trimmed away with a scalpel leaving an overlapping seamline of about 2 rtm width.
The film-wrapped mandrel was then placed into an oven set at 381°C
for 6 minutes, after which it was removed from the oven and allowed to cool. The mandrel was then removed from the finished intraluminal graft. A 10 cm length of the intraluminal graft was pressure tested at 1.0 kg/cm2 for 30 seconds without any adverse visible effects.
A length of 12.5 mm wide tape was cut from the same film used to construct Example 1. The strip of tape was cut so that the biaxially-oriented fibrils of the film were oriented substantially parallel and perpendicular to the length of the tape. The tape was then helically wrapped around the surface of a 6 mm stainless steel mandrel as shown by Figure 6 to form an intraluminal graft of about 16 cm length.
Adjacent tape edges overlapped by about 1 mm. The film-wrapped mandrel was then placed into an oven set at 380°C for 10 minutes after which it was removed and allowed to cool. The mandrel was then removed from the finished intraluminal graft. A 17 cm length of the graft was then pressure tested at 1.0 kg/cm2 for 3 minutes. The pressure test caused no visible damage to the graft.
An intraluminal graft was formed from the film described by Figure 4. This film had a fibril length of about 5 microns, a thickness of about 0.6 mm and a density of 0.3 g/cc. This film is _ available as a filtration membrane from W. L. Gore ~ Associates, Inc., Elkton, MD, part no. 10382. A 7 cm length of this film was wrapped around a 6 mm stainless steel mandrel to form a longitudinally-oriented seamline of about 1 mm width as shown by Figure 7A. A 1 mm wide strip of 0.013 mm thick FEP film was placed between the WO 95!05131 PCT/L1S94/04807 ~~. ~~54~~
overlapped edges of the multiaxially-oriented porous PTFE film. The film-covered mandrel was placed into an oven set at 353°C for 4.5 minutes, removed and allowed to cool. Excess material was trimmed from the 1 mm wide seamline at this time. The mandrel was then removed from the finished intraluminal graft. A 5 cm length of this graft was then pressure tested at 1.0 kg/cm2 for 30 seconds without visible damage.
As previously described, the intraluminal graft may be provided with longitudinal reinforcing ribs in the form of stringers of, for example, FEP or PTFE. Figure 9A describes a cross sectional view of an intraluminal graft with ribs ,~ on the exterior surface. Figure 9B describes a cross sectional view of an intraluminal graft with ribs ~ on the luminal surface. Figure 9C shows a cross sectional view having ribs ,~ between two layers of film. The ribs are not limited to being oriented parallel to the longitudinal axis of the intraluminal graft, but may also be provided to be oriented substantially circumferential to the tube, for example helically oriented. Alternatively, as shown by Figure 10 a braid ~ may used as an additional reinforcing component in place of the reinforcing ribs.
Figures 9A, 9B and 9C describe cross sectional views of the intraluminal graft incorporating reinforcing ribs.
Figure 10 describes a perspective view of the intraluminal graft incorporating a reinforcing braid.
DETAILED DESCRIPTION OF THE INYENTION
Figure 1 shows an enlarged schematic representation of the surface microstructure of a multiaxially-oriented film ~0 having biaxially-oriented fibrils wherein nodes ,~1_ are connected by fibrils 13 and fibrils ~5. Fibrils ~3_ and ~5 are oriented respectively in two directions which are substantially perpendicular to each other within the plane of the film. These multiaxially-oriented films having biaxially-oriented fibrils may also contain some fibrils such as fibril 17 that are not parallel to either fibrils ~ or fibrils ~5.
Figure 2 describes an enlarged schematic representation of the surface microstructure of a multiaxially-oriented film ~0 wherein nodes ~ 1 are connected by fi bri l s ,~,~. The f i bri l s ~, are multiaxially-oriented fibrils which are oriented in substantially all directions within the plane of the film wherein virtually all fibrils are oriented substantially perpendicular to some other fibrils.
Figure 3 shows a scanning electron photomicrograph of a multiaxially-oriented porous expanded PTFE film having biaxially-oriented fibrils used to construct examples 1 and 2 described below.
Figure 4 shows a scanning electron photomicrograph of a multiaxially-oriented porous expanded PTFE film having multiaxially-oriented fibrils used to construct example 3 described below.
The tubular intraluminal graft is manufactured by wrapping a multiaxially-oriented porous expanded PTFE film around a mandrel and , forming a seamline by overlapping adjacent edges of the film. As shown by Figure 5, the seamline 51 may be longitudinally-oriented so that it is substantially parallel to the longitudinal axis 53 of the graft 50. After the seamline 51 is formed, the film-wrapped mandrel is placed into an oven set above the melt-point of the PTFE film 55 for a time adequate to cause the overlapping edges of the film to adhere to each other. After heating, the film-wrapped mandrel is removed from the oven and allowed to cool. The mandrel is then removed from within the resulting tubular intraluminal graft.
Alternatively, an adhesive such as FEP may be used between the.
adjacent edges forming the seamline, requiring that the film-wrapped mandrel be heated only adequately to melt the adhesive enough to bond the adjacent edges.
In still another alternative, the PTFE film may be provided with a coating of the adhesive on only one surface of the film.
These adhesive-coated films are oriented during wrapping of the mandrel so that the adhesive-coated side of the film faces away from the surface of the mandrel and therefore contacts only adjacent layers of film and does not contact the mandrel. The adhesive is preferably in the form of a discontinuous coating in order to have a minimal effect on the porosity of the completed thin wall intraluminal graft. The adhesive must be biocompatible; preferred adhesives are thermoplastics of lower melt point than the crystalline melt point of the PTFE film.
Thermoplastic fluoropolymers such as FEP are most preferred.
These types of adhesives are activated by placing the film-wrapped mandrel into an oven at a combination of time and temperature adequate to cause melting of the adhesive.
The FEP-coated porous expanded PTFE film is made by a process which comprises the steps of: .
a) contacting a porous PTFE film with another layer which is preferably a film of FEP or alternatively of another .thermoplastic polymer;
b) heating the composition obtained in step a) to a temperature above the melting point of the thermoplastic polymer;
c) stretching the heated composition of step b) while maintaining the temperature above the melting point of the thermoplastic polymer; and d) cooling the product of step c).
The adhesive coating on the multiaxially-oriented porous expanded PTFE film may be either continuous (non-porous) or discontinuous (porous) depending primarily on the amount and rate of stretching, the WO 95/05131 PC'1'/US94104807 ~1~9~~~
temperature during stretching and the thickness of the adhesive prior to stretching.
As described by Figure 6, the intraluminal graft ~0 may be formed by wrapping a tape ~~, formed by cutting a multiaxially-oriented porous expanded PTFE film into a narrow strip, helically-wrapping the tape 6~ around a mandrel and overlapping adjacent edges of the tape to create a helically-oriented seamline ~. The overlapping adjacent edges may be adhered as described previously for the longitudinally-oriented seamlines 51.
Figure 7A shows a cross section of the intraluminal graft 5Q
having a simple overlapped seamline ~. In an alternative embodiment described by the cross sectional view of Figure 7B, the seamline ~
may be formed as a flange ~ which may optionally be folded over as shown by the cross sectional view of Figure 7C. The seamlines of Figures 7B and 7C are most practical for longitudinally-oriented seamlines; the simple overlapped edge seamline of Figure 7A is preferred for helically-oriented seamlines.
As shown by the cross sectional view of Figure 8, the intraluminal graft may also be made from two or more layers of multiaxially-oriented porous expanded PTFE film by allowing the film to completely overlap itself at least one time. Two or more layer embodiments may be formed by either helically or longitudinally wrapping the film around the mandrel.
lfarious samples of the intraluminal graft of the present invention were constructed and are described below as examples. The methods used to characterize the fibril lengths of the films used to make the grafts, the wall thicknesses of the films and the resulting grafts, and the method used to mechanically test the integrity of the resulting grafts are as follows.
The fibril lengths of the porous expanded PTFE films referred to herein were estimated mean values obtained by examining scanning electron photomicrographs of these films. For multiaxially-oriented films, these estimates included consideration of fibrils oriented in all directions. The mean fibril lengths of the films used to construct the intraluminal grafts of the present invention are ' preferred to be within range of about 5 to about 120 microns, although fibril lengths beyond this range may also be useful.
_g_ Wall thickness measurements of the finished intraluminal grafts were made by longitudinally slitting the wall of a short length of the tubular graft to create a flat sheet. These wall thickness measurements did not include the overlapped edges of the seamlines.
Seamlines are not included in wail thickness measurements unless the width of the seamline is such that the graft is made from two or more layers of film as described by the cross sectional view of Figure 8.
The wall thickness of the flat sheet was measured using a Mitutoyo model no. 2804-10 snap gauge having a part no. 7300 frame, by placing the sheet between the pads of the gauge and gently easing the pads into contact with the sample until the pads were in full contact with the sheet under the full force of the spring-driven snap gauge pads.
Film density values were based on the bulk volume of a film sample using the snap-gauge thickness measurement.
Pressure testing of all samples was accomplished by inserting a length of 6 mm outside diameter tubular latex bladder of about 0.4 mm wall thickness into the lumen of the tubular sample to be tested, clamping off one end of the tubular sample and latex bladder assembly with forceps, and applying air pressure for a period of time as described for each example to the tubular sample and bladder assembly.
Approximately three seconds was required to achieve the described air pressure level; this three second period was not included in the test period. After the release of pressure, the bladder was removed from the tubular sample and the sample was visually inspected for any resulting damage.
A multiaxially-oriented porous expanded PTFE film having biaxially-oriented fibrils as described by Figures 1 and 3 was used to make an intraluminal graft. The film used was of about 30 micron fibril length, about 10 cm width and about .08 mm thickness. A 12 cm long sample of this film was wrapped around a 6 mm diameter stainless steel mandrel forming a longitudinally-oriented seamline as shown by Figures 7B and 7C. The biaxially-oriented fibrils of the film were oriented to be parallel to the circumference of the mandrel and parallel to the longitudinal axis of the mandrel. The film edges were ~:~~~4~
-lo-adhered by using a hot iron shielded with a thin sheet of polyimide film. The iron, having a surface temperature of about 400°C, was applied by hand against the thin sheet of polyimide film and the length of the seamline. The excess material was then trimmed away with a scalpel leaving an overlapping seamline of about 2 rtm width.
The film-wrapped mandrel was then placed into an oven set at 381°C
for 6 minutes, after which it was removed from the oven and allowed to cool. The mandrel was then removed from the finished intraluminal graft. A 10 cm length of the intraluminal graft was pressure tested at 1.0 kg/cm2 for 30 seconds without any adverse visible effects.
A length of 12.5 mm wide tape was cut from the same film used to construct Example 1. The strip of tape was cut so that the biaxially-oriented fibrils of the film were oriented substantially parallel and perpendicular to the length of the tape. The tape was then helically wrapped around the surface of a 6 mm stainless steel mandrel as shown by Figure 6 to form an intraluminal graft of about 16 cm length.
Adjacent tape edges overlapped by about 1 mm. The film-wrapped mandrel was then placed into an oven set at 380°C for 10 minutes after which it was removed and allowed to cool. The mandrel was then removed from the finished intraluminal graft. A 17 cm length of the graft was then pressure tested at 1.0 kg/cm2 for 3 minutes. The pressure test caused no visible damage to the graft.
An intraluminal graft was formed from the film described by Figure 4. This film had a fibril length of about 5 microns, a thickness of about 0.6 mm and a density of 0.3 g/cc. This film is _ available as a filtration membrane from W. L. Gore ~ Associates, Inc., Elkton, MD, part no. 10382. A 7 cm length of this film was wrapped around a 6 mm stainless steel mandrel to form a longitudinally-oriented seamline of about 1 mm width as shown by Figure 7A. A 1 mm wide strip of 0.013 mm thick FEP film was placed between the WO 95!05131 PCT/L1S94/04807 ~~. ~~54~~
overlapped edges of the multiaxially-oriented porous PTFE film. The film-covered mandrel was placed into an oven set at 353°C for 4.5 minutes, removed and allowed to cool. Excess material was trimmed from the 1 mm wide seamline at this time. The mandrel was then removed from the finished intraluminal graft. A 5 cm length of this graft was then pressure tested at 1.0 kg/cm2 for 30 seconds without visible damage.
As previously described, the intraluminal graft may be provided with longitudinal reinforcing ribs in the form of stringers of, for example, FEP or PTFE. Figure 9A describes a cross sectional view of an intraluminal graft with ribs ,~ on the exterior surface. Figure 9B describes a cross sectional view of an intraluminal graft with ribs ~ on the luminal surface. Figure 9C shows a cross sectional view having ribs ,~ between two layers of film. The ribs are not limited to being oriented parallel to the longitudinal axis of the intraluminal graft, but may also be provided to be oriented substantially circumferential to the tube, for example helically oriented. Alternatively, as shown by Figure 10 a braid ~ may used as an additional reinforcing component in place of the reinforcing ribs.
Claims (22)
1. An intraluminal graft comprising a tube having an exterior surface, a luminal surface, and a longitudinal axis, said tube being comprised of at least one layer of porous expanded polytetrafluoroethylene film wherein the porous expanded polytetrafluoroethylene film has edges and has a microstructure having fibrils oriented in at least two directions which are substantially perpendicular to each other, and wherein said tube has a wall thickness of less than about 0.25 mm,
2. An intraluminal graft according to claim 1 wherein the tube has a seamline formed by overlapping the edges of the porous expanded polytetrafluoroethylene film.
3. An intraluminal graft according to claim 2 wherein the seamline is substantially parallel to the longitudinal axis of the tube.
4. An intraluminal graft according to claim 2 wherein the seamline is helically oriented with respect to the longitudinal axis of the tube.
5. An intraluminal graft according to claim 1 wherein the tube has a wall thickness of less than about 0.1 mm.
6. An intraluminal graft according to claim 2 wherein the tube has a wall thickness of less than about 0.1 mm.
7. An intraluminal graft according to claim 3 wherein the tube has a wall thickness of less than about 0.1 mm.
8. An intraluminal graft according to claim 4 wherein the tube has a wall thickness of less than about 0.1 mm.
9. An intraluminal graft according to claim 5 wherein the tube has a wall thickness of less than about 0.08 mm.
10. An intraluminal graft according to claim 6 wherein the tube has a wall thickness of less than about 0.08 mm.
11. An intraluminal graft according to claim 7 wherein the tube has a wall thickness of less than about 0.08 mm.
12. An intraluminal graft according to claim 8 wherein the tube has a wall thickness of less than about 0.08 mm.
13. An intraluminal graft according to claim 2 wherein the seamline is adhered by an adhesive.
14. An intraluminal graft according to claim 13 wherein the adhesive is fluorinated ethylene propylene.
15. An intraluminal graft according to claim 1 wherein the tube is provided with at least one reinforcing rib.
16. An intraluminal graft according to claim 2 wherein the tube is provided with at least one reinforcing rib.
17. An intraluminal graft according to claim 5 wherein the tube is provided with at least one reinforcing rib.
18. An intraluminal graft according to claim 6 wherein the tube is provided with at least one reinforcing rib.
19. An intraluminal graft according to claim 1 wherein the tube is provided with a reinforcing braid.
20. An intraluminal graft according to claim 2 wherein the tube is provided with a reinforcing braid.
21. An intraluminal graft according to claim 5 wherein the tube is provided with a reinforcing braid.
22. An intraluminal graft according to claim 6 wherein the tube is provided with a reinforcing braid.
Applications Claiming Priority (3)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US10896793A | 1993-08-18 | 1993-08-18 | |
US08/108,967 | 1993-08-18 | ||
PCT/US1994/004807 WO1995005131A1 (en) | 1993-08-18 | 1994-05-04 | A tubular intraluminal graft |
Publications (2)
Publication Number | Publication Date |
---|---|
CA2169549A1 CA2169549A1 (en) | 1995-02-23 |
CA2169549C true CA2169549C (en) | 2000-07-11 |
Family
ID=22325101
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
CA 2169549 Expired - Lifetime CA2169549C (en) | 1993-08-18 | 1994-05-04 | A tubular intraluminal graft |
Country Status (7)
Country | Link |
---|---|
US (2) | US5718973A (en) |
EP (1) | EP0714270B1 (en) |
JP (1) | JPH09501583A (en) |
AU (1) | AU6987594A (en) |
CA (1) | CA2169549C (en) |
DE (1) | DE69431302T2 (en) |
WO (1) | WO1995005131A1 (en) |
Families Citing this family (228)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
WO1995005131A1 (en) * | 1993-08-18 | 1995-02-23 | W.L. Gore & Associates, Inc. | A tubular intraluminal graft |
CA2182500A1 (en) * | 1994-02-17 | 1995-08-24 | Norman J. Sharber | A carvable ptfe implant material |
US6331188B1 (en) | 1994-08-31 | 2001-12-18 | Gore Enterprise Holdings, Inc. | Exterior supported self-expanding stent-graft |
US6015429A (en) | 1994-09-08 | 2000-01-18 | Gore Enterprise Holdings, Inc. | Procedures for introducing stents and stent-grafts |
US6451047B2 (en) | 1995-03-10 | 2002-09-17 | Impra, Inc. | Encapsulated intraluminal stent-graft and methods of making same |
US6579314B1 (en) * | 1995-03-10 | 2003-06-17 | C.R. Bard, Inc. | Covered stent with encapsulated ends |
US6264684B1 (en) | 1995-03-10 | 2001-07-24 | Impra, Inc., A Subsidiary Of C.R. Bard, Inc. | Helically supported graft |
AUPN228395A0 (en) * | 1995-04-11 | 1995-05-04 | Hart, Vincent G. | Artificial arterial-venous graft |
US5641373A (en) * | 1995-04-17 | 1997-06-24 | Baxter International Inc. | Method of manufacturing a radially-enlargeable PTFE tape-reinforced vascular graft |
AU6396496A (en) * | 1995-07-07 | 1997-02-10 | W.L. Gore & Associates, Inc. | Interior liner for tubes, pipes and blood conduits |
CA2229537A1 (en) * | 1995-08-24 | 1997-03-06 | Impra, Inc. | Covered endoluminal stent and method of assembly |
US5788626A (en) * | 1995-11-21 | 1998-08-04 | Schneider (Usa) Inc | Method of making a stent-graft covered with expanded polytetrafluoroethylene |
JP2000503559A (en) | 1995-12-14 | 2000-03-28 | ゴア エンタープライズ ホールディングス,インコーポレイティド | Apparatus and method for deploying a stent-graft |
US6042605A (en) * | 1995-12-14 | 2000-03-28 | Gore Enterprose Holdings, Inc. | Kink resistant stent-graft |
US5800512A (en) * | 1996-01-22 | 1998-09-01 | Meadox Medicals, Inc. | PTFE vascular graft |
US6428571B1 (en) * | 1996-01-22 | 2002-08-06 | Scimed Life Systems, Inc. | Self-sealing PTFE vascular graft and manufacturing methods |
NL1003178C2 (en) * | 1996-05-21 | 1997-11-25 | Cordis Europ | Tubular prosthesis made of curable material. |
DE69734667T2 (en) | 1996-09-26 | 2006-06-08 | Boston Scientific Scimed, Inc., Maple Grove | COMBINED MEDICAL DEVICE CONSISTING OF A SUPPORT STRUCTURE AND A MEMBRANE |
US6010529A (en) * | 1996-12-03 | 2000-01-04 | Atrium Medical Corporation | Expandable shielded vessel support |
US5925074A (en) | 1996-12-03 | 1999-07-20 | Atrium Medical Corporation | Vascular endoprosthesis and method |
US6187039B1 (en) * | 1996-12-10 | 2001-02-13 | Purdue Research Foundation | Tubular submucosal graft constructs |
US6551350B1 (en) * | 1996-12-23 | 2003-04-22 | Gore Enterprise Holdings, Inc. | Kink resistant bifurcated prosthesis |
US6352561B1 (en) | 1996-12-23 | 2002-03-05 | W. L. Gore & Associates | Implant deployment apparatus |
IT1289815B1 (en) * | 1996-12-30 | 1998-10-16 | Sorin Biomedica Cardio Spa | ANGIOPLASTIC STENT AND RELATED PRODUCTION PROCESS |
US6951572B1 (en) * | 1997-02-20 | 2005-10-04 | Endologix, Inc. | Bifurcated vascular graft and method and apparatus for deploying same |
US7628795B2 (en) | 1997-09-24 | 2009-12-08 | Atrium Medical Corporation | Tunneling device for use with a graft |
US6565594B1 (en) | 1997-09-24 | 2003-05-20 | Atrium Medical Corporation | Tunneling device |
US6889082B2 (en) | 1997-10-09 | 2005-05-03 | Orqis Medical Corporation | Implantable heart assist system and method of applying same |
US6395019B2 (en) * | 1998-02-09 | 2002-05-28 | Trivascular, Inc. | Endovascular graft |
US6651670B2 (en) | 1998-02-13 | 2003-11-25 | Ventrica, Inc. | Delivering a conduit into a heart wall to place a coronary vessel in communication with a heart chamber and removing tissue from the vessel or heart wall to facilitate such communication |
US20020144696A1 (en) | 1998-02-13 | 2002-10-10 | A. Adam Sharkawy | Conduits for use in placing a target vessel in fluid communication with a source of blood |
US6808498B2 (en) | 1998-02-13 | 2004-10-26 | Ventrica, Inc. | Placing a guide member into a heart chamber through a coronary vessel and delivering devices for placing the coronary vessel in communication with the heart chamber |
DE69933560T2 (en) * | 1998-06-19 | 2007-08-30 | Endologix, Inc., Irvine | SELF-EXPANDING, CRUSHING, ENOVOVASCULAR PROSTHESIS |
US6461380B1 (en) | 1998-07-28 | 2002-10-08 | Advanced Cardiovascular Systems, Inc. | Stent configuration |
US6187036B1 (en) | 1998-12-11 | 2001-02-13 | Endologix, Inc. | Endoluminal vascular prosthesis |
US6660030B2 (en) * | 1998-12-11 | 2003-12-09 | Endologix, Inc. | Bifurcation graft deployment catheter |
CA2350499C (en) | 1998-12-11 | 2008-01-29 | Endologix, Inc. | Endoluminal vascular prosthesis |
US6733523B2 (en) * | 1998-12-11 | 2004-05-11 | Endologix, Inc. | Implantable vascular graft |
US20020065546A1 (en) * | 1998-12-31 | 2002-05-30 | Machan Lindsay S. | Stent grafts with bioactive coatings |
US20050171594A1 (en) * | 1998-12-31 | 2005-08-04 | Angiotech International Ag | Stent grafts with bioactive coatings |
EP1073384B1 (en) * | 1999-01-22 | 2008-04-02 | Gore Enterprise Holdings, Inc. | Low profile stent and graft combination |
ATE326197T1 (en) * | 1999-01-22 | 2006-06-15 | Gore Enterprise Holdings Inc | COVERED ENDOPROSTHESIS |
US6517571B1 (en) | 1999-01-22 | 2003-02-11 | Gore Enterprise Holdings, Inc. | Vascular graft with improved flow surfaces |
US6673102B1 (en) | 1999-01-22 | 2004-01-06 | Gore Enterprises Holdings, Inc. | Covered endoprosthesis and delivery system |
US6558414B2 (en) | 1999-02-02 | 2003-05-06 | Impra, Inc. | Partial encapsulation of stents using strips and bands |
US6398803B1 (en) | 1999-02-02 | 2002-06-04 | Impra, Inc., A Subsidiary Of C.R. Bard, Inc. | Partial encapsulation of stents |
US6261316B1 (en) | 1999-03-11 | 2001-07-17 | Endologix, Inc. | Single puncture bifurcation graft deployment system |
US8034100B2 (en) * | 1999-03-11 | 2011-10-11 | Endologix, Inc. | Graft deployment system |
US6364903B2 (en) | 1999-03-19 | 2002-04-02 | Meadox Medicals, Inc. | Polymer coated stent |
US6673103B1 (en) | 1999-05-20 | 2004-01-06 | Scimed Life Systems, Inc. | Mesh and stent for increased flexibility |
US6364904B1 (en) * | 1999-07-02 | 2002-04-02 | Scimed Life Systems, Inc. | Helically formed stent/graft assembly |
US6652570B2 (en) * | 1999-07-02 | 2003-11-25 | Scimed Life Systems, Inc. | Composite vascular graft |
US20010018609A1 (en) * | 1999-08-11 | 2001-08-30 | Scott Smith | Seamless braided or spun stent cover |
US6342294B1 (en) * | 1999-08-12 | 2002-01-29 | Bruce G. Ruefer | Composite PTFE article and method of manufacture |
US6383171B1 (en) | 1999-10-12 | 2002-05-07 | Allan Will | Methods and devices for protecting a passageway in a body when advancing devices through the passageway |
US6264671B1 (en) * | 1999-11-15 | 2001-07-24 | Advanced Cardiovascular Systems, Inc. | Stent delivery catheter and method of use |
US8458879B2 (en) | 2001-07-03 | 2013-06-11 | Advanced Bio Prosthetic Surfaces, Ltd., A Wholly Owned Subsidiary Of Palmaz Scientific, Inc. | Method of fabricating an implantable medical device |
US6936066B2 (en) * | 1999-11-19 | 2005-08-30 | Advanced Bio Prosthetic Surfaces, Ltd. | Complaint implantable medical devices and methods of making same |
US6296661B1 (en) * | 2000-02-01 | 2001-10-02 | Luis A. Davila | Self-expanding stent-graft |
US6379382B1 (en) | 2000-03-13 | 2002-04-30 | Jun Yang | Stent having cover with drug delivery capability |
US6613082B2 (en) | 2000-03-13 | 2003-09-02 | Jun Yang | Stent having cover with drug delivery capability |
US6736838B1 (en) * | 2000-03-22 | 2004-05-18 | Zuli Holdings Ltd. | Method and apparatus for covering a stent |
GB2393660B (en) * | 2000-03-22 | 2004-05-26 | Zuli Holdings Ltd | Covered stents |
US6729356B1 (en) * | 2000-04-27 | 2004-05-04 | Endovascular Technologies, Inc. | Endovascular graft for providing a seal with vasculature |
US6616689B1 (en) | 2000-05-03 | 2003-09-09 | Advanced Cardiovascular Systems, Inc. | Intravascular stent |
US6800089B1 (en) * | 2000-05-31 | 2004-10-05 | Advanced Cardiovascular Systems, Inc. | Mechanical attachment method of cover materials on stents |
US6808533B1 (en) | 2000-07-28 | 2004-10-26 | Atrium Medical Corporation | Covered stent and method of covering a stent |
JP3835146B2 (en) * | 2000-09-13 | 2006-10-18 | フジノン株式会社 | Flexible tube and manufacturing method thereof |
US6833153B1 (en) * | 2000-10-31 | 2004-12-21 | Advanced Cardiovascular Systems, Inc. | Hemocompatible coatings on hydrophobic porous polymers |
US7807210B1 (en) | 2000-10-31 | 2010-10-05 | Advanced Cardiovascular Systems, Inc. | Hemocompatible polymers on hydrophobic porous polymers |
WO2002039888A2 (en) * | 2000-11-15 | 2002-05-23 | Endologix, Inc. | Implantable vascular graft |
US6945991B1 (en) * | 2000-11-28 | 2005-09-20 | Boston Scientific/Scimed Life Systems, Inc. | Composite tubular prostheses |
US6929660B1 (en) | 2000-12-22 | 2005-08-16 | Advanced Cardiovascular Systems, Inc. | Intravascular stent |
US6641607B1 (en) | 2000-12-29 | 2003-11-04 | Advanced Cardiovascular Systems, Inc. | Double tube stent |
US6761700B2 (en) | 2001-02-09 | 2004-07-13 | Orqis Medical Corporation | Extra-corporeal vascular conduit |
US7374571B2 (en) | 2001-03-23 | 2008-05-20 | Edwards Lifesciences Corporation | Rolled minimally-invasive heart valves and methods of manufacture |
US6733525B2 (en) * | 2001-03-23 | 2004-05-11 | Edwards Lifesciences Corporation | Rolled minimally-invasive heart valves and methods of use |
US6673105B1 (en) * | 2001-04-02 | 2004-01-06 | Advanced Cardiovascular Systems, Inc. | Metal prosthesis coated with expandable ePTFE |
US6756007B2 (en) | 2001-04-04 | 2004-06-29 | Bard Peripheral Vascular, Inc. | Method for preparing an implantable prosthesis for loading into a delivery apparatus |
US7828833B2 (en) | 2001-06-11 | 2010-11-09 | Boston Scientific Scimed, Inc. | Composite ePTFE/textile prosthesis |
US6629994B2 (en) | 2001-06-11 | 2003-10-07 | Advanced Cardiovascular Systems, Inc. | Intravascular stent |
US7560006B2 (en) * | 2001-06-11 | 2009-07-14 | Boston Scientific Scimed, Inc. | Pressure lamination method for forming composite ePTFE/textile and ePTFE/stent/textile prostheses |
US6939373B2 (en) | 2003-08-20 | 2005-09-06 | Advanced Cardiovascular Systems, Inc. | Intravascular stent |
EP1399200B2 (en) * | 2001-06-11 | 2014-07-02 | Boston Scientific Limited | COMPOSITE ePTFE/TEXTILE PROSTHESIS |
US6635083B1 (en) | 2001-06-25 | 2003-10-21 | Advanced Cardiovascular Systems, Inc. | Stent with non-linear links and method of use |
US6749629B1 (en) | 2001-06-27 | 2004-06-15 | Advanced Cardiovascular Systems, Inc. | Stent pattern with figure-eights |
US6716239B2 (en) * | 2001-07-03 | 2004-04-06 | Scimed Life Systems, Inc. | ePTFE graft with axial elongation properties |
US7060023B2 (en) * | 2001-09-25 | 2006-06-13 | The Foundry Inc. | Pericardium reinforcing devices and methods of using them |
US20030074055A1 (en) * | 2001-10-17 | 2003-04-17 | Haverkost Patrick A. | Method and system for fixation of endoluminal devices |
US6814561B2 (en) | 2001-10-30 | 2004-11-09 | Scimed Life Systems, Inc. | Apparatus and method for extrusion of thin-walled tubes |
US7597775B2 (en) | 2001-10-30 | 2009-10-06 | Boston Scientific Scimed, Inc. | Green fluoropolymer tube and endovascular prosthesis formed using same |
GB2384189A (en) * | 2001-11-21 | 2003-07-23 | Tayside Flow Technologies Ltd | Helix shaped insert for flow moification in a duct or stent |
US6776604B1 (en) | 2001-12-20 | 2004-08-17 | Trivascular, Inc. | Method and apparatus for shape forming endovascular graft material |
US7125464B2 (en) * | 2001-12-20 | 2006-10-24 | Boston Scientific Santa Rosa Corp. | Method for manufacturing an endovascular graft section |
US7147661B2 (en) * | 2001-12-20 | 2006-12-12 | Boston Scientific Santa Rosa Corp. | Radially expandable stent |
WO2003053288A1 (en) * | 2001-12-20 | 2003-07-03 | Trivascular, Inc. | Advanced endovascular graft |
US7090693B1 (en) | 2001-12-20 | 2006-08-15 | Boston Scientific Santa Rosa Corp. | Endovascular graft joint and method for manufacture |
US7139385B2 (en) * | 2002-01-18 | 2006-11-21 | Sbc Technology Resources, Inc. | Method for NPA split processing on a service control point |
US6929768B2 (en) * | 2002-05-13 | 2005-08-16 | Advanced Cardiovascular Systems, Inc. | Method of making a catheter balloon by laser fusing wrapped material |
US6656220B1 (en) | 2002-06-17 | 2003-12-02 | Advanced Cardiovascular Systems, Inc. | Intravascular stent |
US7335184B2 (en) * | 2002-07-02 | 2008-02-26 | Sentient Engineering And Technology | Balloon catheter and treatment apparatus |
US6878329B2 (en) * | 2002-07-30 | 2005-04-12 | Advanced Cardiovascular Systems, Inc. | Method of making a catheter balloon using a polyimide covered mandrel |
US7029495B2 (en) * | 2002-08-28 | 2006-04-18 | Scimed Life Systems, Inc. | Medical devices and methods of making the same |
US20040059406A1 (en) * | 2002-09-20 | 2004-03-25 | Cully Edward H. | Medical device amenable to fenestration |
US7025791B2 (en) | 2002-12-02 | 2006-04-11 | Gi Dynamics, Inc. | Bariatric sleeve |
EP1569582B1 (en) * | 2002-12-02 | 2017-05-31 | GI Dynamics, Inc. | Bariatric sleeve |
US7608114B2 (en) * | 2002-12-02 | 2009-10-27 | Gi Dynamics, Inc. | Bariatric sleeve |
US7678068B2 (en) * | 2002-12-02 | 2010-03-16 | Gi Dynamics, Inc. | Atraumatic delivery devices |
US8088158B2 (en) * | 2002-12-20 | 2012-01-03 | Boston Scientific Scimed, Inc. | Radiopaque ePTFE medical devices |
CN1732022A (en) * | 2002-12-30 | 2006-02-08 | 血管技术国际股份公司 | Silk stent grafts |
US7318836B2 (en) | 2003-03-11 | 2008-01-15 | Boston Scientific Scimed, Inc. | Covered stent |
US8333798B2 (en) | 2003-11-07 | 2012-12-18 | Merlin Md Pte Ltd. | Implantable medical devices with enhanced visibility, mechanical properties and biocompatability |
EP1689457A2 (en) * | 2003-11-10 | 2006-08-16 | Angiotech International Ag | Intravascular devices and fibrosis-inducing agents |
WO2005060882A1 (en) | 2003-12-09 | 2005-07-07 | Gi Dynamics, Inc. | Apparatus to be anchored within the gastrointestinal tract and anchoring method |
US20050131515A1 (en) * | 2003-12-16 | 2005-06-16 | Cully Edward H. | Removable stent-graft |
US7854756B2 (en) * | 2004-01-22 | 2010-12-21 | Boston Scientific Scimed, Inc. | Medical devices |
US7803178B2 (en) | 2004-01-30 | 2010-09-28 | Trivascular, Inc. | Inflatable porous implants and methods for drug delivery |
US20050228484A1 (en) * | 2004-03-11 | 2005-10-13 | Trivascular, Inc. | Modular endovascular graft |
US8500751B2 (en) | 2004-03-31 | 2013-08-06 | Merlin Md Pte Ltd | Medical device |
US8715340B2 (en) * | 2004-03-31 | 2014-05-06 | Merlin Md Pte Ltd. | Endovascular device with membrane |
WO2005094725A1 (en) | 2004-03-31 | 2005-10-13 | Merlin Md Pte Ltd | A method for treating aneurysms |
US7955373B2 (en) * | 2004-06-28 | 2011-06-07 | Boston Scientific Scimed, Inc. | Two-stage stent-graft and method of delivering same |
JP4856067B2 (en) * | 2004-07-09 | 2012-01-18 | ジーアイ・ダイナミックス・インコーポレーテッド | Method and apparatus for positioning a gastrointestinal sleeve |
US7765670B2 (en) * | 2004-08-13 | 2010-08-03 | Boston Scientific Scimed, Inc. | Method to simultaneously load and cover self expanding stents |
US7063720B2 (en) * | 2004-09-14 | 2006-06-20 | The Wallace Enterprises, Inc. | Covered stent with controlled therapeutic agent diffusion |
US8029563B2 (en) * | 2004-11-29 | 2011-10-04 | Gore Enterprise Holdings, Inc. | Implantable devices with reduced needle puncture site leakage |
WO2006033641A1 (en) * | 2004-12-22 | 2006-03-30 | Merlin Md Pte Ltd | A medical device |
US7524445B2 (en) * | 2004-12-31 | 2009-04-28 | Boston Scientific Scimed, Inc. | Method for making ePTFE and structure containing such ePTFE, such as a vascular graft |
US7857843B2 (en) | 2004-12-31 | 2010-12-28 | Boston Scientific Scimed, Inc. | Differentially expanded vascular graft |
US7806922B2 (en) | 2004-12-31 | 2010-10-05 | Boston Scientific Scimed, Inc. | Sintered ring supported vascular graft |
US9320831B2 (en) * | 2005-03-04 | 2016-04-26 | W. L. Gore & Associates, Inc. | Polymer shrink tubes and novel uses therefor |
US20060233990A1 (en) * | 2005-04-13 | 2006-10-19 | Trivascular, Inc. | PTFE layers and methods of manufacturing |
US20060233991A1 (en) | 2005-04-13 | 2006-10-19 | Trivascular, Inc. | PTFE layers and methods of manufacturing |
GB0511431D0 (en) | 2005-06-04 | 2005-07-13 | Vascutek Ltd | Graft |
US7963988B2 (en) * | 2005-06-23 | 2011-06-21 | Boston Scientific Scimed, Inc. | ePTFE lamination—resizing ePTFE tubing |
US20070049804A1 (en) * | 2005-08-25 | 2007-03-01 | Albert Wong | One-piece retractable stent |
US7655035B2 (en) * | 2005-10-05 | 2010-02-02 | Boston Scientific Scimed, Inc. | Variable lamination of vascular graft |
US20070128243A1 (en) * | 2005-12-02 | 2007-06-07 | Xylos Corporation | Implantable microbial cellulose materials for various medical applications |
US20070179599A1 (en) * | 2006-01-31 | 2007-08-02 | Icon Medical Corp. | Vascular protective device |
JP4750860B2 (en) * | 2006-02-13 | 2011-08-17 | マーリン エムディー ピーティーイー リミテッド | Intravascular device having a membrane |
US8585753B2 (en) * | 2006-03-04 | 2013-11-19 | John James Scanlon | Fibrillated biodegradable prosthesis |
US7709631B2 (en) | 2006-03-13 | 2010-05-04 | Xylos Corporation | Oxidized microbial cellulose and use thereof |
US20070286884A1 (en) * | 2006-06-13 | 2007-12-13 | Xylos Corporation | Implantable microbial cellulose materials for hard tissue repair and regeneration |
US9408607B2 (en) | 2009-07-02 | 2016-08-09 | Edwards Lifesciences Cardiaq Llc | Surgical implant devices and methods for their manufacture and use |
WO2008016578A2 (en) | 2006-07-31 | 2008-02-07 | Cartledge Richard G | Sealable endovascular implants and methods for their use |
US9585743B2 (en) | 2006-07-31 | 2017-03-07 | Edwards Lifesciences Cardiaq Llc | Surgical implant devices and methods for their manufacture and use |
US20080071343A1 (en) * | 2006-09-15 | 2008-03-20 | Kevin John Mayberry | Multi-segmented graft deployment system |
US8778009B2 (en) | 2006-10-06 | 2014-07-15 | Abbott Cardiovascular Systems Inc. | Intravascular stent |
US8523931B2 (en) * | 2007-01-12 | 2013-09-03 | Endologix, Inc. | Dual concentric guidewire and methods of bifurcated graft deployment |
US8646444B2 (en) * | 2007-03-27 | 2014-02-11 | Electrolux Home Products, Inc. | Glide rack |
US7608186B2 (en) * | 2007-03-30 | 2009-10-27 | General Electric Company | Coated asymmetric membrane system having oleophobic and hydrophilic properties |
US20080237117A1 (en) * | 2007-03-30 | 2008-10-02 | Vishal Bansal | Coated asymmetric membrane system having oleophobic and hydrophilic properties |
US8087923B1 (en) | 2007-05-18 | 2012-01-03 | C. R. Bard, Inc. | Extremely thin-walled ePTFE |
US9566178B2 (en) | 2010-06-24 | 2017-02-14 | Edwards Lifesciences Cardiaq Llc | Actively controllable stent, stent graft, heart valve and method of controlling same |
US9814611B2 (en) | 2007-07-31 | 2017-11-14 | Edwards Lifesciences Cardiaq Llc | Actively controllable stent, stent graft, heart valve and method of controlling same |
US20090082845A1 (en) * | 2007-09-26 | 2009-03-26 | Boston Scientific Corporation | Alignment stent apparatus and method |
US20090082841A1 (en) * | 2007-09-26 | 2009-03-26 | Boston Scientific Corporation | Apparatus for securing stent barbs |
US8066755B2 (en) * | 2007-09-26 | 2011-11-29 | Trivascular, Inc. | System and method of pivoted stent deployment |
US8226701B2 (en) | 2007-09-26 | 2012-07-24 | Trivascular, Inc. | Stent and delivery system for deployment thereof |
US8663309B2 (en) * | 2007-09-26 | 2014-03-04 | Trivascular, Inc. | Asymmetric stent apparatus and method |
JP2010540190A (en) | 2007-10-04 | 2010-12-24 | トリバスキュラー・インコーポレイテッド | Modular vascular graft for low profile transdermal delivery |
US8083789B2 (en) * | 2007-11-16 | 2011-12-27 | Trivascular, Inc. | Securement assembly and method for expandable endovascular device |
US8328861B2 (en) | 2007-11-16 | 2012-12-11 | Trivascular, Inc. | Delivery system and method for bifurcated graft |
WO2009086200A1 (en) * | 2007-12-20 | 2009-07-09 | Trivascular2, Inc. | Hinged endovascular device |
US8221494B2 (en) | 2008-02-22 | 2012-07-17 | Endologix, Inc. | Apparatus and method of placement of a graft or graft system |
US8196279B2 (en) * | 2008-02-27 | 2012-06-12 | C. R. Bard, Inc. | Stent-graft covering process |
US8236040B2 (en) * | 2008-04-11 | 2012-08-07 | Endologix, Inc. | Bifurcated graft deployment systems and methods |
EP2293838B1 (en) | 2008-07-01 | 2012-08-08 | Endologix, Inc. | Catheter system |
US8262692B2 (en) * | 2008-09-05 | 2012-09-11 | Merlin Md Pte Ltd | Endovascular device |
DE102009003890A1 (en) * | 2009-01-02 | 2010-07-08 | Bioregeneration Gmbh | Apparatus comprising a device and a liner implantable in a vessel of the body of a patient, and methods of making same |
US20130268062A1 (en) | 2012-04-05 | 2013-10-10 | Zeus Industrial Products, Inc. | Composite prosthetic devices |
US20120059399A1 (en) * | 2009-03-10 | 2012-03-08 | The John Hopkins University | Biological tissue connection and repair devices and methods of using same |
US8142145B2 (en) * | 2009-04-21 | 2012-03-27 | Thut Bruno H | Riser clamp for pumps for pumping molten metal |
US8945202B2 (en) | 2009-04-28 | 2015-02-03 | Endologix, Inc. | Fenestrated prosthesis |
US9579103B2 (en) * | 2009-05-01 | 2017-02-28 | Endologix, Inc. | Percutaneous method and device to treat dissections |
US10772717B2 (en) | 2009-05-01 | 2020-09-15 | Endologix, Inc. | Percutaneous method and device to treat dissections |
WO2011008989A2 (en) | 2009-07-15 | 2011-01-20 | Endologix, Inc. | Stent graft |
US8118856B2 (en) | 2009-07-27 | 2012-02-21 | Endologix, Inc. | Stent graft |
JP2013501539A (en) | 2009-08-07 | 2013-01-17 | ゼウス インダストリアル プロダクツ インコーポレイテッド | Prosthetic device comprising an electrospun fiber layer and method for producing the same |
US20110218609A1 (en) * | 2010-02-10 | 2011-09-08 | Trivascular, Inc. | Fill tube manifold and delivery methods for endovascular graft |
US20110218617A1 (en) * | 2010-03-02 | 2011-09-08 | Endologix, Inc. | Endoluminal vascular prosthesis |
US8636811B2 (en) * | 2010-04-07 | 2014-01-28 | Medtronic Vascular, Inc. | Drug eluting rolled stent and stent delivery system |
US8696738B2 (en) | 2010-05-20 | 2014-04-15 | Maquet Cardiovascular Llc | Composite prosthesis with external polymeric support structure and methods of manufacturing the same |
WO2012061526A2 (en) | 2010-11-02 | 2012-05-10 | Endologix, Inc. | Apparatus and method of placement of a graft or graft system |
WO2012068298A1 (en) | 2010-11-17 | 2012-05-24 | Endologix, Inc. | Devices and methods to treat vascular dissections |
DK3011936T3 (en) * | 2011-01-06 | 2019-05-20 | Humacyte | Tissue Manipulated Structures |
US10166128B2 (en) | 2011-01-14 | 2019-01-01 | W. L. Gore & Associates. Inc. | Lattice |
US9839540B2 (en) | 2011-01-14 | 2017-12-12 | W. L. Gore & Associates, Inc. | Stent |
JP6294669B2 (en) | 2011-03-01 | 2018-03-14 | エンドロジックス、インク | Catheter system and method of use thereof |
US9744033B2 (en) | 2011-04-01 | 2017-08-29 | W.L. Gore & Associates, Inc. | Elastomeric leaflet for prosthetic heart valves |
US9579224B2 (en) * | 2011-07-25 | 2017-02-28 | Neograft Technologies, Inc. | Vessel remodeling methods and devices for use in a graft device |
US9554806B2 (en) | 2011-09-16 | 2017-01-31 | W. L. Gore & Associates, Inc. | Occlusive devices |
US9827093B2 (en) | 2011-10-21 | 2017-11-28 | Edwards Lifesciences Cardiaq Llc | Actively controllable stent, stent graft, heart valve and method of controlling same |
US9510935B2 (en) * | 2012-01-16 | 2016-12-06 | W. L. Gore & Associates, Inc. | Articles including expanded polytetrafluoroethylene membranes with serpentine fibrils and having a discontinuous fluoropolymer layer thereon |
JP5997294B2 (en) * | 2012-01-16 | 2016-09-28 | ダブリュ.エル.ゴア アンド アソシエイツ,インコーポレイティドW.L. Gore & Associates, Incorporated | Article comprising a stretched polytetrafluoroethylene membrane having serpentine fibrils and having a discontinuous fluoropolymer layer thereon |
US9775933B2 (en) | 2012-03-02 | 2017-10-03 | W. L. Gore & Associates, Inc. | Biocompatible surfaces and devices incorporating such surfaces |
US9554989B2 (en) * | 2012-03-20 | 2017-01-31 | Trustees Of Tufts College | Silk reservoirs for drug delivery |
US8992595B2 (en) | 2012-04-04 | 2015-03-31 | Trivascular, Inc. | Durable stent graft with tapered struts and stable delivery methods and devices |
JP6324371B2 (en) | 2012-04-06 | 2018-05-16 | マーリン エムディー プライベート リミテッド | Devices and methods for treating aneurysms |
US9498363B2 (en) | 2012-04-06 | 2016-11-22 | Trivascular, Inc. | Delivery catheter for endovascular device |
US9283072B2 (en) | 2012-07-25 | 2016-03-15 | W. L. Gore & Associates, Inc. | Everting transcatheter valve and methods |
US9931193B2 (en) | 2012-11-13 | 2018-04-03 | W. L. Gore & Associates, Inc. | Elastic stent graft |
US9144492B2 (en) | 2012-12-19 | 2015-09-29 | W. L. Gore & Associates, Inc. | Truncated leaflet for prosthetic heart valves, preformed valve |
US9101469B2 (en) | 2012-12-19 | 2015-08-11 | W. L. Gore & Associates, Inc. | Prosthetic heart valve with leaflet shelving |
US9968443B2 (en) | 2012-12-19 | 2018-05-15 | W. L. Gore & Associates, Inc. | Vertical coaptation zone in a planar portion of prosthetic heart valve leaflet |
US10279084B2 (en) | 2012-12-19 | 2019-05-07 | W. L. Gore & Associates, Inc. | Medical balloon devices and methods |
ES2973834T3 (en) * | 2013-04-13 | 2024-06-24 | Solinas Medical Inc | Automatic closing devices, and apparatus and methods for manufacturing and supplying the same |
US9629978B2 (en) * | 2013-05-20 | 2017-04-25 | Clph, Llc | Catheters with intermediate layers and methods for making them |
US11911258B2 (en) | 2013-06-26 | 2024-02-27 | W. L. Gore & Associates, Inc. | Space filling devices |
US9814560B2 (en) | 2013-12-05 | 2017-11-14 | W. L. Gore & Associates, Inc. | Tapered implantable device and methods for making such devices |
US10842918B2 (en) | 2013-12-05 | 2020-11-24 | W.L. Gore & Associates, Inc. | Length extensible implantable device and methods for making such devices |
US9827094B2 (en) | 2014-09-15 | 2017-11-28 | W. L. Gore & Associates, Inc. | Prosthetic heart valve with retention elements |
EP3977945A1 (en) | 2015-05-14 | 2022-04-06 | W. L. Gore & Associates, Inc. | Devices for occlusion of an atrial appendage |
BR112017025950A2 (en) | 2015-06-05 | 2018-08-14 | W. L. Gore & Associates, Inc. | ? low bleed implantable prosthesis with a taper? |
EP4417169A2 (en) | 2015-06-30 | 2024-08-21 | Endologix LLC | Locking assembly for coupling guidewire to delivery system |
WO2017184153A1 (en) | 2016-04-21 | 2017-10-26 | W. L. Gore & Associates, Inc. | Diametrically adjustable endoprostheses and associated systems and methods |
EP3318223B1 (en) * | 2016-11-02 | 2020-09-23 | Biotronik AG | Device for embedding a balloon arranged on a catheter into an implant and corresponding method |
US10238513B2 (en) | 2017-07-19 | 2019-03-26 | Abbott Cardiovascular Systems Inc. | Intravascular stent |
CA3071133C (en) | 2017-09-12 | 2023-02-28 | W.L. Gore & Associates, Inc. | Leaflet frame attachment for prosthetic valves |
JP7068444B2 (en) | 2017-09-27 | 2022-05-16 | ダブリュ.エル.ゴア アンド アソシエイツ,インコーポレイティド | Artificial valves with expandable frames, as well as related systems and methods |
JP6875601B2 (en) | 2017-09-27 | 2021-05-26 | ダブリュ.エル.ゴア アンド アソシエイツ,インコーポレイティドW.L. Gore & Associates, Incorporated | Artificial valve with mechanically coupled leaflet |
WO2019074607A1 (en) | 2017-10-13 | 2019-04-18 | W. L. Gore & Associates, Inc. | Telescoping prosthetic valve and delivery system |
US11173023B2 (en) | 2017-10-16 | 2021-11-16 | W. L. Gore & Associates, Inc. | Medical devices and anchors therefor |
AU2018362079B2 (en) | 2017-10-31 | 2021-09-16 | Edwards Lifesciences Corporation | Medical valve and leaflet promoting tissue ingrowth |
US11497601B2 (en) | 2019-03-01 | 2022-11-15 | W. L. Gore & Associates, Inc. | Telescoping prosthetic valve with retention element |
WO2020204184A1 (en) * | 2019-04-05 | 2020-10-08 | 株式会社 潤工社 | Method for providing basic product and mandrel covered with long body |
US11324583B1 (en) | 2021-07-06 | 2022-05-10 | Archo Medical LTDA | Multi-lumen stent-graft and related surgical methods |
CN114176855B (en) * | 2021-12-13 | 2023-12-19 | 中国科学院长春应用化学研究所 | Degradable polymer ultrathin membrane, preparation method and application thereof, and preparation method of covered vascular stent |
Family Cites Families (65)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US2016962A (en) * | 1932-09-27 | 1935-10-08 | Du Pont | Process for producing glucamines and related products |
US2844609A (en) * | 1955-06-29 | 1958-07-22 | Onyx Oil & Chemical Company | Preparation of amides |
US3657744A (en) * | 1970-05-08 | 1972-04-25 | Univ Minnesota | Method for fixing prosthetic implants in a living body |
CA962021A (en) * | 1970-05-21 | 1975-02-04 | Robert W. Gore | Porous products and process therefor |
US3868956A (en) * | 1972-06-05 | 1975-03-04 | Ralph J Alfidi | Vessel implantable appliance and method of implanting it |
US6436135B1 (en) * | 1974-10-24 | 2002-08-20 | David Goldfarb | Prosthetic vascular graft |
DE2654658A1 (en) * | 1975-12-02 | 1977-06-08 | Rhone Poulenc Ind | IMPLANTABLE SURGICAL LEAD |
FR2333487A1 (en) * | 1975-12-02 | 1977-07-01 | Rhone Poulenc Ind | Implantable surgical tubing with sewable ends - has radially elastic wall including a fleece layer and reinforcement |
US4208745A (en) * | 1976-01-21 | 1980-06-24 | Sumitomo Electric Industries, Ltd. | Vascular prostheses composed of polytetrafluoroethylene and process for their production |
JPS6039917B2 (en) * | 1976-11-26 | 1985-09-07 | 日東電工株式会社 | Expandable tube for covering objects |
US4140126A (en) * | 1977-02-18 | 1979-02-20 | Choudhury M Hasan | Method for performing aneurysm repair |
US4130904A (en) * | 1977-06-06 | 1978-12-26 | Thermo Electron Corporation | Prosthetic blood conduit |
US4190909A (en) * | 1978-03-31 | 1980-03-04 | Ablaza Sariel G G | Apparatus and method for surgical repair of dissecting thoracic aneurysms and the like |
JPS6037733B2 (en) * | 1978-10-12 | 1985-08-28 | 住友電気工業株式会社 | Tubular organ prosthesis material and its manufacturing method |
AU5179879A (en) * | 1978-10-17 | 1980-04-24 | Unasco Pty. Ltd. | Pipe jointing or sealing compositions |
US4283448A (en) * | 1980-02-14 | 1981-08-11 | W. L. Gore & Associates, Inc. | Composite polytetrafluoroethylene article and a process for making the same |
JPS6028434Y2 (en) * | 1980-06-16 | 1985-08-28 | 建部 容保 | Artificial blood vessel |
DE3250058C2 (en) * | 1981-09-16 | 1992-08-27 | Medinvent S.A., Lausanne, Ch | |
IT1139824B (en) * | 1981-11-23 | 1986-09-24 | Victor Slicing System Srl | AUTOMATIC SLICER FOR SALAMI AND SIMILAR PRODUCTS |
DE3214447C2 (en) * | 1982-04-20 | 1994-05-11 | Eilentropp Hew Kabel | Unsintered wrapping tape of polytetrafluoroethylene |
SE445884B (en) * | 1982-04-30 | 1986-07-28 | Medinvent Sa | DEVICE FOR IMPLANTATION OF A RODFORM PROTECTION |
US4478898A (en) * | 1982-06-04 | 1984-10-23 | Junkosha Co., Ltd. | Laminated porous polytetrafluoroethylene tube and its process of manufacture |
JPS6017230A (en) * | 1983-07-07 | 1985-01-29 | Kazuyoshi Miyasaka | Electrolytic internal-combustion engine |
US4550447A (en) * | 1983-08-03 | 1985-11-05 | Shiley Incorporated | Vascular graft prosthesis |
US4787899A (en) * | 1983-12-09 | 1988-11-29 | Lazarus Harrison M | Intraluminal graft device, system and method |
US5275622A (en) * | 1983-12-09 | 1994-01-04 | Harrison Medical Technologies, Inc. | Endovascular grafting apparatus, system and method and devices for use therewith |
JPS60172306A (en) * | 1984-02-17 | 1985-09-05 | Daikin Ind Ltd | Compound film |
US4562596A (en) * | 1984-04-25 | 1986-01-07 | Elliot Kornberg | Aortic graft, device and method for performing an intraluminal abdominal aortic aneurysm repair |
US4577631A (en) * | 1984-11-16 | 1986-03-25 | Kreamer Jeffry W | Aneurysm repair apparatus and method |
US4733665C2 (en) * | 1985-11-07 | 2002-01-29 | Expandable Grafts Partnership | Expandable intraluminal graft and method and apparatus for implanting an expandable intraluminal graft |
US4681110A (en) * | 1985-12-02 | 1987-07-21 | Wiktor Dominik M | Catheter arrangement having a blood vessel liner, and method of using it |
US4878906A (en) * | 1986-03-25 | 1989-11-07 | Servetus Partnership | Endoprosthesis for repairing a damaged vessel |
US4743480A (en) * | 1986-11-13 | 1988-05-10 | W. L. Gore & Associates, Inc. | Apparatus and method for extruding and expanding polytetrafluoroethylene tubing and the products produced thereby |
DE3711776A1 (en) * | 1987-04-08 | 1988-10-27 | Huels Chemische Werke Ag | USE OF N-POLYHYDROXYALKYL Fatty Acid Amides As Thickeners For Liquid Aqueous Surfactant Systems |
US4816339A (en) * | 1987-04-28 | 1989-03-28 | Baxter International Inc. | Multi-layered poly(tetrafluoroethylene)/elastomer materials useful for in vivo implantation |
US5061276A (en) * | 1987-04-28 | 1991-10-29 | Baxter International Inc. | Multi-layered poly(tetrafluoroethylene)/elastomer materials useful for in vivo implantation |
US4820298A (en) * | 1987-11-20 | 1989-04-11 | Leveen Eric G | Internal vascular prosthesis |
US4877030A (en) * | 1988-02-02 | 1989-10-31 | Andreas Beck | Device for the widening of blood vessels |
US4925710A (en) * | 1988-03-31 | 1990-05-15 | Buck Thomas F | Ultrathin-wall fluoropolymer tube with removable fluoropolymer core |
US5078726A (en) * | 1989-02-01 | 1992-01-07 | Kreamer Jeffry W | Graft stent and method of repairing blood vessels |
US5152782A (en) * | 1989-05-26 | 1992-10-06 | Impra, Inc. | Non-porous coated ptfe graft |
DE3918736C2 (en) * | 1989-06-08 | 1998-05-14 | Christian Dr Vallbracht | Plastic-coated metal mesh stents |
DE69110787T2 (en) * | 1990-02-28 | 1996-04-04 | Medtronic, Inc., Minneapolis, Minn. | INTRALUMINAL PROSTHESIS WITH ACTIVE ELEMENTATION. |
DE69103264T2 (en) * | 1990-03-15 | 1994-11-24 | Gore & Ass | CATHETER CLOTHING AND METHOD FOR THEIR PRODUCTION. |
US5107852A (en) * | 1990-04-02 | 1992-04-28 | W. L. Gore & Associates, Inc. | Catheter guidewire device having a covering of fluoropolymer tape |
US5123917A (en) * | 1990-04-27 | 1992-06-23 | Lee Peter Y | Expandable intraluminal vascular graft |
EP0461791B1 (en) * | 1990-06-11 | 1997-01-02 | Hector D. Barone | Aortic graft and apparatus for repairing an abdominal aortic aneurysm |
US5098779A (en) * | 1990-06-25 | 1992-03-24 | W. L. Gore & Associates, Inc. | Carvable implant material |
US5236447A (en) * | 1990-06-29 | 1993-08-17 | Nissho Corporation | Artificial tubular organ |
US5122154A (en) * | 1990-08-15 | 1992-06-16 | Rhodes Valentine J | Endovascular bypass graft |
US5449372A (en) * | 1990-10-09 | 1995-09-12 | Scimed Lifesystems, Inc. | Temporary stent and methods for use and manufacture |
CA2052981C (en) * | 1990-10-09 | 1995-08-01 | Cesare Gianturco | Percutaneous stent assembly |
US5156620A (en) * | 1991-02-04 | 1992-10-20 | Pigott John P | Intraluminal graft/stent and balloon catheter for insertion thereof |
US5282847A (en) * | 1991-02-28 | 1994-02-01 | Medtronic, Inc. | Prosthetic vascular grafts with a pleated structure |
DK0528039T3 (en) * | 1991-03-08 | 1999-12-13 | Keiji Igaki | Stent for vessels, structure for holding the stent and device for mounting the stent |
CA2065634C (en) * | 1991-04-11 | 1997-06-03 | Alec A. Piplani | Endovascular graft having bifurcation and apparatus and method for deploying the same |
US5151105A (en) * | 1991-10-07 | 1992-09-29 | Kwan Gett Clifford | Collapsible vessel sleeve implant |
EP0539237A1 (en) * | 1991-10-25 | 1993-04-28 | Cook Incorporated | Expandable transluminal graft prosthesis for repair of aneurysm and method for implanting |
US5211658A (en) * | 1991-11-05 | 1993-05-18 | New England Deaconess Hospital Corporation | Method and device for performing endovascular repair of aneurysms |
DE69325649T2 (en) * | 1992-03-13 | 1999-11-18 | Atrium Medical Corp., Hollis | OBJECTS OF EXPANDED FLUOROPOLYMER (e.g. POLYTETRAFLUORETHYLENE) WITH CONTROLLED POROSITY AND ITS PRODUCTION |
US5269810A (en) * | 1992-06-19 | 1993-12-14 | W. L. Gore & Associates, Inc. | Patch electrode |
EP0714345B1 (en) * | 1993-08-18 | 2001-09-12 | W.L. Gore & Associates, Inc. | A thin-wall, seamless, porous polytetrafluoroethylene tube |
US5735892A (en) * | 1993-08-18 | 1998-04-07 | W. L. Gore & Associates, Inc. | Intraluminal stent graft |
WO1995005131A1 (en) * | 1993-08-18 | 1995-02-23 | W.L. Gore & Associates, Inc. | A tubular intraluminal graft |
US6124523A (en) * | 1995-03-10 | 2000-09-26 | Impra, Inc. | Encapsulated stent |
-
1994
- 1994-05-04 WO PCT/US1994/004807 patent/WO1995005131A1/en active IP Right Grant
- 1994-05-04 CA CA 2169549 patent/CA2169549C/en not_active Expired - Lifetime
- 1994-05-04 AU AU69875/94A patent/AU6987594A/en not_active Abandoned
- 1994-05-04 EP EP94918646A patent/EP0714270B1/en not_active Expired - Lifetime
- 1994-05-04 JP JP50692694A patent/JPH09501583A/en active Pending
- 1994-05-04 DE DE69431302T patent/DE69431302T2/en not_active Expired - Lifetime
-
1995
- 1995-07-26 US US08/508,213 patent/US5718973A/en not_active Expired - Lifetime
-
1998
- 1998-02-17 US US09/024,239 patent/US5993489A/en not_active Expired - Lifetime
Also Published As
Publication number | Publication date |
---|---|
DE69431302D1 (en) | 2002-10-10 |
WO1995005131A1 (en) | 1995-02-23 |
CA2169549A1 (en) | 1995-02-23 |
EP0714270A1 (en) | 1996-06-05 |
US5993489A (en) | 1999-11-30 |
EP0714270B1 (en) | 2002-09-04 |
JPH09501583A (en) | 1997-02-18 |
DE69431302T2 (en) | 2003-05-15 |
US5718973A (en) | 1998-02-17 |
AU6987594A (en) | 1995-03-14 |
Similar Documents
Publication | Publication Date | Title |
---|---|---|
CA2169549C (en) | A tubular intraluminal graft | |
US6159565A (en) | Thin-wall intraluminal graft | |
US5735892A (en) | Intraluminal stent graft | |
CA2226635C (en) | Interior liner for tubes, pipes and blood conduits | |
EP1207815A1 (en) | Tubular stent-graft composite device and method of manufacture | |
EP1767169A1 (en) | Tubular stent-graft composite device and method of manufacture |
Legal Events
Date | Code | Title | Description |
---|---|---|---|
EEER | Examination request | ||
MKEX | Expiry |
Effective date: 20140505 |